Targeted contrast agents for mri of amyloid deposition

ABSTRACT

A liposomal composition (“ADx-001”) is provided, ADx-001 comprising a first phospholipid; a sterically bulky excipient that is capable of stabilizing the liposomal composition; a second phospholipid that is derivatized with a first polymer; a macrocyclic gadolinium-based imaging agent; and a third phospholipid that is derivatized with a second polymer, the second polymer being conjugated to a targeting ligand. The macrocyclic gadolinium-based imaging agent may be conjugated to a fourth phospholipid.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application claims priority from U.S. Provisional PatentApplication No. 62/967,295, filed on Jan. 29, 2020, which isincorporated by reference herein in its entirety.

STATEMENT REGARDING FEDERALLY SPONSORED RESEARCH OR DEVELOPMENT

This invention was made with U.S. Government support under Contract Nos.R44AG051292, U01DE028233, and R01HD094347 awarded by the NationalInstitutes of Health. The U.S. Government has certain rights in theinvention.

BACKGROUND

A definitive diagnosis of Alzheimer's disease (“AD”) requires postmortemneuropathological demonstration of β-amyloid plaques and neurofibrillarytau tangles. However, advances in the development of position emissiontomography (“PET”) imaging probes for these biomarkers have facilitateda new research framework to study and characterize the disease in vivo.Although not approved for clinical diagnosis, this framework, advancedby the National Institute of Aging and Alzheimer's Associated, definesbiological AD by either in vivo PET imaging or other biomarker evidenceof β-amyloid plaques and neurofibrillary tau tangles. The use oftargeted PET tracers in clinical research has dramatically improvedunderstanding of the evolution of AD biomarkers in the context ofdementia. The clinical deployment of such non-invasive imaging ADbiomarkers may enable early diagnosis of AD-related dementia andfacilitate early intervention.

The build-up of β-amyloid plaques in the brain is one of the earliestpathogenic events in AD. Pre-clinical and clinical studies using PETprobes have demonstrated that parenchymal deposition of amyloid plaquesbegins decades before clinical presentation of cognitive impairment inAD-related dementia. Furthermore, the formation of amyloid plaques hasbeen causally linked to the pathogenesis of neurofibrillary tau tangles.Although amyloid imaging PET probes, such as 18F-florbetaben,18F-florbetapir, and 18F-flutemetamol have substantially advancedunderstanding of AD pathophysiology leading to cognitive impairment andare playing a critical role in clinical trials for the evaluation ofdisease-modifying investigational therapies, accessibility to PETmodalities for the general population remains a worldwide problem. Anamyloid imaging agent for use with magnetic resonance imaging (“MRI”)could be transformative due to ease of accessibility and comparativelylow cost.

A high T1 relaxivity, amyloid-targeted liposomal-gadolinium (Gd)nanoparticle contrast agent (containing a first linear Gd chelate,Gd-DTPA bis(stearylamide) (“Gd-DTPA-BSA”), conjugated on the internaland external surfaces of the liposome bilayer, and a second linear Gdchelate, gadobenate dimeglumine (“Gd-BOPTA”), in the core interior ofthe liposomes) has enabled in vivo MRI of amyloid plaques in transgenicmouse models of AD. See WO2016057812A1 and Ghaghada K B, Ravoori M,Sabapathy D, Bankson J, Kundra V, et al. (2009) New Dual Mode GadoliniumNanoparticle Contrast Agent for Magnetic Resonance Imaging, PLoS ONE4(10); e7628 Doi:10.1371/journal.pone.0007628, each of which isincorporated by reference herein in its entirety. However, evidence hasemerged of brain deposition of Gd dissociated from such linear chelates.Thus, a more stable targeted liposomal Gd contrast agent for MRI ofamyloid plaques is needed.

SUMMARY

In one aspect, a liposomal composition (“ADx-001”) is provided, ADx-001comprising a first phospholipid; a sterically bulky excipient that iscapable of stabilizing the liposomal composition; a second phospholipidthat is derivatized with a first polymer; a macrocyclic gadolinium-basedimaging agent; and a third phospholipid that is derivatized with asecond polymer, the second polymer being conjugated to a targetingligand, the targeting ligand being represented by:

wherein,

Pyrimidine “P” may be substituted with zero, one, or more of —OH,O-alkyl, and —NH₂;

R² is a linking group comprising C₁-C₆ alkyl or C₁-C₆ alkoxyalkyl; and

R³ is hydrogen, C₁-C₆ alkyl, or C₁-C₆ alkoxyalkyl, and R³ other thanhydrogen is substituted with zero, one, or more —OH.

In a further aspect, the first phospholipid comprises hydrogenated soyL-α-phosphatidylcholine (“HSPC”); the sterically bulky excipient that iscapable of stabilizing the liposomal composition comprises cholesterol(“Chol”); the second phospholipid that is derivatized with a firstpolymer comprises1,2-distearoyl-sn-glycero-3-phosphoethanolamine-N-(methoxy (polyethyleneglycol)-2000) (“DSPE-mPEG2000”); and the macrocyclic gadolinium-basedimaging agent comprises gadolinium(3+)2-[4,7,10-tris(carboxylatomethyl)-1,4,7,10-tetrazacyclododec-1-yl]acetate(“gadoterate” or “Gd(III)-DOTA”) and is conjugated to a fourthphospholipid, e.g.:

or a salt (e.g., a sodium salt) thereof. In some aspects, the variable xmay be one of: 12, 13, 14, 15, 16, 17, or 18. In one aspect, thevariable x is 16 (the conjugate: “Gd(III)-DOTA-DSPE”). In some aspects,the third phospholipid that is derivatized with a second polymer, thesecond polymer being conjugated to the targeting ligand, may comprise:

or a salt (e.g., an ammonium phosphate salt) thereof. In some aspects,the variable n may be any integer from about 10 to about 100, forexample, about 60 to about 100, about 70 to about 90, about 75 to about85, about 77, or about 79. The variable m may be one of: 12, 13, 14, 15,16, 17, or 18. For example, n may be 77, and m may be 14; n may be 79,and m may be 14; n may be 77, and m may be 16; and n may be 79, and mmay be 16.

In one aspect, the targeting ligand comprises:

In one aspect, n is 79, m is 16 (“DSPE-PEG3500”), and the targetingligand comprises Compound iii:

(the conjugate: “ET3-73”), including as a salt (e.g., an ammoniumphosphate salt) thereof.

In one aspect, a method for imaging amyloid deposits in a subject isprovided. The method may comprise introducing in the subject adetectable quantity of liposomal composition. The method may compriseallowing sufficient time for the liposomal composition to be associatedwith one or more amyloid deposits. The method may comprise detecting theliposomal composition associated with the one or more amyloid deposits.

In one aspect, the liposomal composition of the method for imagingamyloid deposits in a subject may comprise ADx-001. In one aspect, theliposomal composition of the method for imaging amyloid deposits in asubject may comprise Gd(III)-DOTA-DSPE and ET3-73. In one aspect, theliposomal composition of the method for imaging amyloid deposits in asubject may comprise HSPC, Chol, DSPE-mPEG2000, Gd(III)-DOTA-DSPE, andET3-73.

In one aspect, the liposomal compositions are suitable for use inimaging amyloid deposits in a patient, the use comprising: introducinginto the patient a detectable quantity of the liposomal composition;allowing sufficient time for the liposomal composition to be associatedwith one or more amyloid deposits; and detecting the liposomalcomposition associated with the one or more amyloid deposits. In oneaspect, the use comprises detecting using MRI.

In one aspect, the use further comprises: identifying the patient aspotentially having AD according to detecting the liposomal compositionassociated with the one or more amyloid deposits; subjecting the patientto an analysis for tau neurofibrillary tangles; and upon determining thepresence of tau neurofibrillary tangles in conjunction with detectingthe liposomal composition associated with the one or more amyloiddeposits, diagnosing the patient with AD.

BRIEF DESCRIPTION OF THE FIGURES

FIG. 1 provides an example cross-sectional depiction of a liposomecomprising a targeted contrast agent for MRI of amyloid deposition.

FIG. 2 shows a representative schematic of the surface conjugatedmacrocyclic Gd-based imaging agent (“SC-Gd”) as described hereincompared to prior art dual Gd liposomes (“Dual-Gd”).

FIG. 3 shows a comparison of T₁ relaxivity of Gd(III) forms at 1T fieldstrength between “free” Gd(III)-DOTA (i.e., not conjugated to aliposome), the prior art Gd(III)-DTPA-BSA liposomes, and theGd(III)-DOTA-DSPE liposomes (i.e., ADx-001 liposomes) as describedherein.

FIG. 4 provides an example synthetic scheme for the synthesis of ET3-73ammonium salt.

FIG. 5 provides an example synthetic scheme for the synthesis ofGd(III)-DOTA-DSPE sodium salt.

FIG. 6 shows an example process flow diagram for the preparation ofADx-001.

FIG. 7 shows a demonstration of cortical regions of interest (ROIs)identification in axial MR images of the brain. Cortical ROIs areoutlined on FSE-IR brain images pre- (upper) and post- (lower) contrast.

FIG. 8 shows pre- and post-ADx-001 administration T1-weighted spin-echo(“T1w-SE”) axial images of the brain: a) of a wild-type (“WT”) mouse(amyloid-negative) at a dose of 0.20 mmol Gd/kg; and of TgAPPswe/PSEN1dE9 (“Tg”) mice (amyloid-positive) at doses of: b) 0.20 mmolGd/kg; c) 0.15 mmol Gd/kg; and d) 0.10 mmol Gd/kg. Arrows point toregions of signal enhancement in the cortex and hippocampus.

FIG. 9 shows pre- and post-ADx-001 administration fast spin-echoinversion recovery (“FSE-IR”) axial images of the brain: a) of a WTmouse at a dose of 0.20 mmol Gd/kg; and of Tg mice at doses of: b) 0.20mmol Gd/kg; c) 0.15 mmol Gd/kg; and d) 0.10 mmol Gd/kg. Arrows point toregions of signal enhancement in the cortex and hippocampus.

FIG. 10 demonstrates that Tg mice exhibit MR signal enhancement incortical brain regions relative to WT counterparts at all dose levels ofADx-001. The box plots show statistically significant differences insignal changes (expressed as percentage) between pre-contrast anddelayed post-contrast T1w-SE images for: a) 0.20 mmol Gd/kg; b) 0.15mmol Gd/kg; and c) 0.10 mmol Gd/kg dose levels of ADx-001, and betweenpre-contrast and delayed post-contrast FSE-IR images for: d) 0.20 mmolGd/kg; e) 0.15 mmol Gd/kg; and f) 0.10 mmol Gd/kg dose levels.

FIG. 11 shows the signal intensity mean and range for (a) T1w-SE and (b)FSE-IR sequences for pre-contrast scans of both WT (n=18) and Tg (n=18)mice. ROIs were drawn in the cortex for each animal. No significantdifferences (NS) were found between signal intensities for WT and Tgmice for either T1w-SE or FSE-IR sequences.

FIG. 12 shows the cortical brain signal change as a function of time inWT (n=3) and Tg (n=3) mice in a) T1w-SE and b) FSE-IR sequences. Maximumsignal enhancement was seen at day 4 post-contrast (arrow). Tg animalsdemonstrated signal enhancement relative to WT animals in bothsequences. The signal returned to near baseline levels by day 21.

FIG. 13 provides post-mortem confirmation of ADx-001 binding toβ-amyloid plaques via representative fluorescence microscopy images ofADx-001 binding to amyloid plaques in a) mouse cortex and b) hippocampusregions in a Tg animal, as compared to representative images for c) WTcortex and d) hippocampus regions in a WT animal.

FIG. 14 shows plasma Gd concentrations determined usinginductively-coupled plasma mass spectrometry (“ICP-MS”) at various timepoints after administration of ADx-001 in dogs (▴) and monkeys (●).

FIG. 15 shows the biodistribution of ADx-001 in a rat a) spleen, b)liver, c) kidney, d) bone, e) skin, and f) brain at day 4 and day 28after intravenous administration of ADx-001 at 0.15 mmol Gd/kg doselevel (▴) and 0.3 mmol Gd/kg dose level (●), as determined by ICP-MSanalysis.

DETAILED DESCRIPTION

A novel amyloid-targeted liposomal-Gd contrast agent, ADx-001, has beendeveloped based on a highly stable macrocyclic Gd-DOTA imaging moiety.ADx-001 may be generally understood as depicted in cross-section form inFIG. 1. FIG. 2 shows a representative schematic of the conjugation ofthe macrocyclic gadolinium-based imaging agent as described herein(“SC-Gd”), with the Gd chelates conjugated on the internal and externalsurfaces of the liposome bilayer, compared to the dual Gd liposomes ofWO2016057812A1, which contain both core-encapsulated andsurface-conjugated Gd chelates, e.g., as described in WO2016057812A1and/or in Tanifum E A, Ghaghada K, Vollert C, Head E, Eriksen J L,Annapragada A. A Novel Liposomal Nanoparticle for the Imaging of AmyloidPlaque by Magnetic Resonance Imaging. J Alzheimer's Dis. 2016.doi:10.3233/JAD-151124, each of which is incorporated by referenceherein in its entirety.

Contrast agents with higher T₁ relaxivities produce strongerenhancement. FIG. 3 shows a comparison of T₁ relaxivity of Gd(III) formsat 1T field strength between “free” Gd(III)-DOTA (i.e., not conjugatedto a liposome), the prior art Gd(III)-DTPA-BSA liposomes, and theGd(III)-DOTA-DSPE liposomes (i.e., ADx-001 liposomes) as describedherein. ADx-001 exhibits ˜3-fold higher T₁ relaxivity compared to theprior art Gd(III)-DTPA-BSA liposomes.

More specifically, liposomal Gd-DOTA, with Gd DOTA conjugated to aphospholipid, exhibits approximately three-fold higher T1 relaxivity(˜31 mM−1 S−1 on a Gd-basis and 2,295,000 mM−1 S−1 on a nanoparticlebasis at 1 T field strength) than liposomal Gd-DTPA (˜9.0 mM−1 S−1 on aGd-basis and 668,000 mM−1 S−1 on a nanoparticle basis at 1 T fieldstrength) where Gd-DTPA is conjugated to bis(stearylamide). Gdconjugation is important on at least three bases. First, conjugation ofGd-chelate to a macromolecule slows the rotational correlation of the Gdatom, and therefore increases the rotational correlation time. A higherrotational correlation time yields higher T1 relaxivity. Second,conjugation of Gd-chelate to a phospholipid (here, DSPE) (Gd-DOTA-DSPE)further increases the rotational correlation time compared to Gd-chelateconjugated to bis(stearylamide) (Gd-DTPA-BSA), and thereforeGd-DOTA-DSPE liposomes perform better (higher T1 relaxivity) compared toGd-DTPA-BSA liposomes. Finally, by conjugating to a true phospholipid,the stability of insertion into the bilayer is greater. In contrast, thelack of the phosphatidyl group in Gd-DTPA-BSA reduces the amphiphilicityof the molecule, and therefore the stability of insertion.

Thus, in one aspect, ADx-001 comprises a first phospholipid; asterically bulky excipient that is capable of stabilizing the liposomalcomposition; a second phospholipid that is derivatized with a firstpolymer; a macrocyclic gadolinium-based imaging agent; and a thirdphospholipid that is derivatized with a second polymer, the secondpolymer being conjugated to a targeting ligand. The macrocyclicgadolinium-based imaging agent may be conjugated to a fourthphospholipid.

Phospholipids

In some aspects, suitable phospholipids include those where the twohydrocarbon chains are between about 14 and about 24 carbon atoms inlength and have varying degrees of unsaturation. In some aspects,suitable phospholipids include HSPC,1,2-dipalmitoyl-sn-glycero-3-phosphocholine (“DPPC”),1,2-distearoyl-sn-glycero-3-phosphocholine (“DSPC”),1,2-distearoyl-sn-glycero-3-phosphoethanolamine (“DSPE”), and mixturesof two or more thereof. Suitable phospholipids may be naturallyoccurring or synthetic.

In some aspects, suitable phospholipids may include any of those listedin WO2005107820A1, the content of paragraphs [0031]-[0033] of which isincorporated by reference herein in its entirety.

Polymer-Derivatized Phospholipids

In some aspects, the liposomes of the liposomal composition may includea surface that contains or is coated with flexible water soluble(hydrophilic) polymer chains. These polymer chains may preventinteraction between the liposomes and blood plasma components, theplasma components playing a role in uptake of liposomes by cells of theblood and removal of the liposomes from the blood. The liposomes mayavoid uptake by the organs of the mononuclear phagocyte system,primarily the liver and spleen (the reticulendothelial system).

In one aspect, the polymer in the derivatized phospholipid may bepolyethylene glycol (“PEG”). The PEG can have any of a variety ofmolecular weights. In one example, the PEG chain may have a molecularweight between about 1,000-10,000 daltons. Once a liposome is formed,the PEG chains may provide a surface coating of hydrophilic chainssufficient to extend the blood circulation time of the liposomes in theabsence of such a coating.

In some aspects, the second phospholipid that is derivatized with afirst polymer comprises DSPE-mPEG2000. In some aspects, the thirdphospholipid that is derivatized with a second polymer, the secondpolymer being conjugated to the targeting ligand, comprises:

or a salt (e.g., an ammonium phosphate salt) thereof, wherein thevariable n may be any integer from about 10 to about 100, for example,about 60 to about 100, about 70 to about 90, about 75 to about 85, about77, or about 79. The variable m may be one of: 12, 13, 14, 15, 16, 17,or 18. For example, n may be 77, and m may be 14; n may be 79, and m maybe 14; n may be 77, and m may be 16; and n may be 79, and m may be 16.In some aspects, the third phospholipid that is derivatized with asecond polymer comprises DSPE-PEG3500.

In some aspects, suitable polymers may include any of those listed inWO2005107820A1, the content of paragraphs [0034]-[0038] of which isincorporated by reference herein in its entirety. In some embodiments,the phospholipid derivatized by a polymer may be any of thosecombinations disclosed in WO2016057812A1.

Sterically Bulky Excipients

In some aspects, the liposomes may include stabilizing excipients. Forexample, the liposomal compositions may be formulated to comprise Chol.In other aspects, the liposomal compositions may comprise fattyalcohols, fatty acids, cholesterol esters, other pharmaceuticallyacceptable excipients, and mixtures thereof.

Macrocyclic Gadolinium-Based Imaging Agents

The liposomal composition comprises a macrocyclic Gd-based imagingagent. In some aspects, the macrocyclic gadolinium-based imaging agentcomprises Gd(III)-DOTA conjugated to a phospholipid, e.g.:

or a salt (e.g., a sodium salt) thereof. In some aspects, the variable xmay be one of: 12, 13, 14, 15, 16, 17, or 18. In one aspect, thevariable x is 16 and the conjugate is Gd(III)-DOTA-DSPE.

In other aspects, the macrocyclic gadolinium-based imaging agentcomprises:

The liposome compositions comprise at least one phospholipid that isderivatized with a polymer, the polymer being conjugated to a targetingligand. Thus, in some aspects, the phospholipid is modified to include aspacer chain. The spacer chain may be a hydrophilic polymer. Thehydrophilic polymer may typically be end-functionalized for coupling tothe targeting ligand. The functionalized end group may be, for example,a maleimide group, a bromoacetamide group, a disulfide group, anactivated ester, or an aldehyde group. Hydrazide groups are reactivetoward aldehydes, which may be generated on numerous biologicallyrelevant compounds. Hydrazides may also be acylated by active esters orcarbodiimide-activated carboxyl groups. Acyl azide groups reactive asacylating species may be easily obtained from hydrazides and permit theattachment of amino containing ligands.

In some aspects, the targeting ligand may be accessible from the surfaceof the liposome and may specifically bind or attach to, for example, oneor more molecules or antigens. These targeting ligands may direct ortarget the liposomes to a specific cell or tissue, e.g., an amyloid-βplaque, and may bind to a molecule or antigen on or associated with thecell or tissue.

The targeting ligand is represented by:

wherein,

Pyrimidine “P” may be substituted with zero, one, or more of —OH,O-alkyl, and —NH₂;

R² is a linking group comprising C₁-C₆ alkyl or C₁-C₆ alkoxyalkyl; and

R³ is hydrogen, C₁-C₆ alkyl, or C₁-C₆ alkoxyalkyl, and R³ other thanhydrogen is substituted with zero, one, or more —OH.

In one aspect, the targeting ligand is Compound iii. In one aspect, thephospholipid-polymer-targeting ligand conjugate is ET3-73.

In further aspects, the targeting ligand is any of Compounds i-xiii asdisclosed in WO2016057812A1. In yet further aspects, the targetingligand is Compound ii, iii, xi, and xiii as disclosed in WO2016057812A1.

Liposomes

“Liposomes” generally refer to spherical or roughly spherical particlescontaining an internal cavity. The walls of liposomes may include abilayer of lipids. These lipids can be phospholipids. Numerous lipidsand/or phospholipids may be used to make liposomes. One example areamphipathic lipids having hydrophobic and polar head group moieties,which may form spontaneously into bilayer vesicles in water, asexemplified by phospholipids, or which may be stably incorporated intolipid bilayers, with their hydrophobic moiety in contact with theinterior, hydrophobic region of the bilayer membrane, and their polarhead group moiety oriented toward the exterior, polar surface of themembrane. Liposomes may be prepared by any known method, including asdescribed in the Examples herein, in WO2016057812A1, and inWO2012139080A1, which is incorporated by reference herein in itsentirety. FIG. 1 provides an example cross-sectional depiction of aliposome comprising a targeted contrast agent for MRI of amyloiddeposition.

In one aspect, ADx-001 comprises: HSPC; Chol; DSPE-mPEG2000; ET3-73; andGd(III)-DOTA-DSPE. In some aspects, the first phospholipid may compriseDPPC, DSPC, or a mixture of DPPC and DSPC. In one aspect, the lipidcomposition and molar ratio (%) of components in ADx-001 areHSPC:Chol:DSPE-mPEG2000:Gd(III)-DOTA-DSPE:ET3-73=about 31.5:about40:about 2.5:about 25:about 1. In some aspects, the molar ratio of anyone of HSPC:Chol:DSPE-mPEG2000:Gd(III)-DOTA-DSPE:ET3-73 may be adjustedby up to 10%, thus, 31.5±10%: 40±10%: 2.5±10%: 25±10%: 1±10%. In oneaspect, the lipid composition and molar ratio (%) of components inADx-001 are HSPC:Chol:DSPE-mPEG2000:Gd(III)-DOTA-DSPE:ET3-73=about32.5:about 40:about 2:about 25:about 0.5.

In one aspect, the HSPC content in ADx-001 is between about 24 mg/mL andabout 32 mg/mL (total lipid). In one aspect, the Chol content in ADx-001is between about 14 mg/mL and about 19 mg/mL. In one aspect, theDSPE-mPEG2000 content in ADx-001 is between about 5 mg/mL and about 7mg/mL. In one aspect, the Gd(III)-DOTA-DSPE content in ADx-001 isbetween 30 mg/mL and 45 mg/mL. In one aspect, the ET3-73 content inADx-001 is between about 2 mg/mL and about 3 mg/mL. In one aspect, thefree gadolinium content in ADx-001 is <100 μg/mL, including <2.5 μg/mL.

In one aspect, the liposomal composition has a pH of between 6.4 and8.4. In a further aspect, the liposomes have an osmolality of between200-400 mOsmol/kg. In a further aspect, the liposomes have vesicle size(Z-average) as measured by dynamic light scattering of less than 200 nm(D₅₀), including less than 150 nm (D₅₀), including about 140 nm (D₅₀),and including about 120 nm (D₅₀).

The term “about” in conjunction with a number is intended to include±10% of the number. This is true whether “about” is modifying astand-alone number or modifying a number at either or both ends of arange of numbers. In other words, “about 10” means from 9 to 11.Likewise, “about 10 to about 20” contemplates 9 to 22 and 11 to 18. Inthe absence of the term “about,” the exact number is intended. In otherwords, “10” means 10.

EXAMPLES

Dose-response, pharmacokinetics, and biodistribution in animal models ofADx-001 were studied. Dose-ranging efficacy studies were performed in aTg mouse model of early-onset AD. Imaging was performed on a 1 Teslapermanent magnet MR scanner using T1w-SE and FSE-IR sequences. ADx-001was tested at three dose levels: 0.10, 0.15, and 0.20 mmol Gd/kg. Tg andage-matched WT control animals (n=6/dose level/genotype) were imagedpre-contrast and at 4 days after administration of ADx-001 (delayedpost-contrast). Pre-contrast and delayed post-contrast images werequalitatively and quantitatively analyzed to determine sensitivity,specificity, and accuracy against post-mortem histologicalidentification of amyloid-β plaque. The pharmacokinetics of ADx-001 werestudied in monkeys and dogs. Blood samples were collected at multipletime points after administration of ADx-001, and Gd levels were analyzedby ICP-MS. The biodistribution of ADx-001 was studied in rats. Gd levelsin target organs (liver, spleen, kidney, skin, bone, and brain) weredetermined by ICP-MS at day 4 and day 28 after administration ofADx-001.

Example 1: Preparation of ET3-73

With reference to FIG. 4, the starting material(E)-2-((2-aminoethyl)(4-(2-(pyrimidin-4-yl)vinyl)phenyl)amino)ethan-1-ol (SM1) was reacted with DIPEA to form ET3-73 Intermediate 1.ET3-73 Intermediate 1 was reacted with TBDMS-OTf (TBDMS-Triflate) toyield ET3-73 Intermediate 2. ET3-73 Intermediate 2 was coupled withHO-PEG3500-NH₂ (SM2) to form ET3-73 Intermediate 3. ET3-73 Intermediate3 was reacted with bis-pentafluorophenyl-carbonate, and the activatedET3-73 Intermediate 3 was combined with DSPE that had been silylatedusing bis-trimethylsilyl-acetamide, to yield ET3-73 Intermediate 4.Finally, the ET3-73 ammonium salt was formed via deprotection usingTBAF, followed by reaction with sodium ammonium acetate.

Example 2: Preparation of Gd(III)-DOTA-DSPE

With reference to FIG. 5, the synthetic scheme starts with the furtheresterification of DOTA-tris(tert-butyl ester) (SM1) withpentafluorophenol (HOpFP). The tert-butyl ester protecting groups wereremoved using TFA and trimethylchlorsilane (TMSCl). Thepentafluorophenyl ester was coupled to DSPE in the presence of BSA andNMM to form DSPE-DOTA. Chelation of gadolinium and salt formationoccurred via addition of gadolinium as an acetate salt [Gd(OAc)3],followed by addition of the scavenger SiliaMetS TAAcONa(Triaminetetraacetate, sodium salt-functionalized silica gel) to formthe final DSPE-DOTA-Gd sodium salt.

Example 3: Preparation of ADx-001

With reference to FIG. 6, ADx-001 was prepared as follows:

Step 1 (buffer solution): Sodium chloride and histidine were dissolvedin water with mixing and filtered through a 0.2 μm filter. The solutionwas nominally pH 7.5.

Step 2 (lipid solution): DSPE-DOTA-Gd, HSPC (Lipoid Inc., Newark, N.J.,USA), DSPE-mPEG₂₀₀₀ (Corden Pharma, Liestahl, Switzerland), Chol (LipoidInc., Newark, N.J., USA), and ET3-73 (31.5:40:2.5:25:1 molar ratio) weredissolved in tert-butyl alcohol with mixing.

Step 3 (liposome formation): The lipid solution (step 2) was added to aportion of the buffer solution (step 1). The pH was adjusted tonominally pH 6.5-7.0 with sodium hydroxide solution, if necessary. Thisstep generated liposomes of indeterminate size and lamellarity. The drugsubstance (DSPE-DOTA-Gd) and the other lipid components (HSPC,DSPE-mPEG₂₀₀₀, Cholesterol, and ET3-73) reside within the lipid bilayerof the liposome.

Step 4 (extrusion): The process material was extruded through track-etchpolycarbonate filters at elevated pressures in order to reduce theliposome vesicle size. Processing continued until the desired vesiclesize (˜140 nm nominal size) was achieved, as measured by an in-processdynamic light scattering test.

Step 5 (ultrafiltration): Ultrafiltration was performed on the processmaterial using a tangential flow filtration assembly with a 500,000molecular weight cut-off (MWCO) rating. During ultrafiltration, theliposome nanoparticles were re-circulated and retained by theultrafilter, while a portion of the carrier solution (buffer solutionplus solvent tert-butyl alcohol) passed through the ultrafilter into thepermeate waste stream. The ultrafiltration step consisted of threesections. First, the process material was concentrated by discarding thepermeate from the ultrafilter. Second, the ultrafiltration assembly wasoperated in a diafiltration mode, in which a constant concentration ismaintained by replenishing the permeate waste stream with buffersolution (step 1). Third, the process material was concentrated in orderto reach a slightly more concentrated level than the nominally 98 mg/mLtotal lipid composition of the final drug product.

Step 6 (prefiltration): The process material was passed throughtrack-etch polycarbonate filters until the desired filterability wasachieved.

Step 7 (clarifying filtration): The process material was passed througha 0.2 μm filter (Sartorius Sartopore® 2 XLI with polyethersulfonemembrane).

Step 8 (dilution): The process material was diluted with buffer solution(Step 1) to the target label strength of 38.7 mg/mL DSPE-DOTA-Gd. Thenominal concentration was 98 mg/L total lipid.

Step 9 (sterile filtration): Under aseptic conditions, the processmaterial was passed through a 0.2 μm sterilizing-grade filter (SartoriusSartopore® 2 XLI with polyethersulfone membrane).

Step 10 (aseptic fill): Under aseptic conditions, the process materialwas filled into vials, stoppered, and sealed. Fill weight checks wereperformed during the filling operation, and filled vials were 100%visually inspected for particulates and container-closure defects. Batchdata for multiple example batches is set forth in Table 1:

TABLE 1 Attrib- Batch Data ute 1 2 3 4 Visual Yellow to off- Yellow tooff- Yellow to off- Yellow to off- Ap- yellow yellow yellow yellow pear-translucent translucent translucent translucent ance liquid, free ofliquid, free of liquid, free of liquid, free of visible visible visiblevisible particulates particulates particulates particulates pH 7.7 7.57.3 7.3 Osmo- 274 mOsmol/ 277 mOsmol/ 295 mOsmol/ 311 mOsmol/ lality kgkg kg kg Vesicle Z-avg: Z-avg: Z-avg: Z-avg: Size 140 nm 98 nm 103 nm115 nm (Dy- D10: 86 nm D₁₀: 63 nm D₁₀: 66 nm D₁₀: 78 nm namic D50: 155nm D₅₀: 106 nm D₅₀: 111 nm D₅₀: 122 nm Light D90: 268 nm D₉₀: 178 nmD₉₀: 189 nm D₉₀: 192 nm Scatter- PDI: 0.2 PDI: 0.1 PDI: 0.1 PDI: 0.1ing) DSPE- 30.78 mg/mL 41.32 mg/mL 38.85 mg/mL 33.73 mg/mL DOTA- GdContent ET3-73  2.22 mg/mL  2.82 mg/mL  2.88 mg/mL  2.29 mg/mL ContentHSPC 23.57 mg/mL 31.49 mg/mL 30.49 mg/mL 28.37 mg/mL Content DSPE-  5.62mg/mL  6.67 mg/mL  6.78 mg/mL  6.32 mg/mL PEG Content Choles- 14.47mg/mL 18.37 mg/mL 18.55 mg/mL 17.07 mg/mL terol Content Stearic <400μg/mL <200 μg/mL <200 μg/mL <200 μg/mL Acid Resid- 13 ppm 12 ppm 16 ppm54 ppm ual Sol- vents Free <2.5 μg/mL <2.5 μg/mL <2.5 μg/mL <2.5 μg/mLGd

Example 4: MRI Study

Studies were performed in an APPswe/PSEN1dE9 (C57BL/6J background, 11-18months age) double Tg mouse model of early-onset AD (JAX MMRRC Stock#005864). The Tg mice develop amyloid plaques in the brain around 6-7months of age. ADx-001, as prepared in Example 3, was tested at threedose levels (mmol Gd/kg): 0.10, 0.15, and 0.20. At each dose level,ADx-001 was tested in Tg (n=6) and WT (mice that lacked both mutations)mice (n=6). ADx-001 was intravenously administered as a slow bolusinjection via tail vein.

Imaging was performed on a 1T permanent MRI scanner (M7 system, AspectImaging, Shoham, Israel). Animals were sedated using 2.5 or 3%isoflurane and placed on a custom fabricated sled with an integratedface-cone for continuous anesthesia delivery by inhalation (1-2%isoflurane). Respiration rate was monitored by a pneumaticallycontrolled pressure pad placed underneath the abdominal region. Two MMsequences were tested: a T1w-SE sequence and a 2D FSE-IR thatapproximates a fluid-attenuated inversion recovery sequence. SEparameters were: TR=600 ms, TE=11.5 ms, slice thickness=1.2 mm,matrix=192×192, FOV=30 mm, slices=16, NEX=4. FSE-IR parameters were:TR=6500 ms, TE=80 ms, TI=2000 ms, slice thickness=2.4 mm,matrix=192×192, FOV=30 mm, slices=6, NEX=6. Coil calibrations, RFcalibration, and shimming were performed at the beginning of the studyfor each subject. All animals underwent pre-contrast scans followed byintravenous administration of ADx-001. Delayed post-contrast scans wereacquired four days after administration of contrast agent. Pre-contrastand post-contrast scans were acquired using both T1w-SE and FSE-IRsequences.

Animals were euthanized after post-contrast scans and perfused with 0.9%saline followed by 4% formalin solution. The brains were excised, fixedin 4% formalin solution for 24 hours, and transferred to 30% sucrose forcryoprotection. Brains were embedded in OCT and stored at −80° C. untilready for sectioning. 15 μm thick brain sections were cut and used forpost-mortem phenotypic confirmation of amyloid deposition. Sections wereincubated in 5% Bovine Serum Albumin (“BSA”) for 1 hour, followed byincubation with fluorescent-tagged anti-amyloid β antibody (AF647-4G8,BioLegend, San Diego, Calif.) in 3% BSA at 4° C. overnight. Sectionswere further stained with a nuclear marker (DAPI), washed, mounted,cover-slipped using Vectashield mounting medium (Vector Laboratories,Burlingame Calif.), and imaged on a confocal microscope with appropriatefilter sets. The presence of amyloid bound ADx-001 nanoparticles wasanalyzed by imaging in FITC channel.

Qualitative and quantitative analyses of MM images were performed inOsiriX (version 5.8.5, 64-bit) and MATLAB (version 2015a). Brainextraction was performed through a combination of threshold and manualsegmentation in OsiriX. Signal change between pre-contrast and delayedpost-contrast images was assessed through quantification of signalintensity in cortical regions near the center of the image stack (seeFIG. 7). Amyloid-positive animals were identified through qualitativeassessment of signal enhancement between pre-contrast and delayedpost-contrast assessment of the cortex and hippocampus. The change insignal between pre-contrast and post-contrast images was quantifiedthrough integration of signal in ROIs that encompassed cortical tissuein central slices of the MRI volume. Signal change (%) was calculated asin Eq. 1:

$\begin{matrix}{{{Signal}\mspace{14mu}{change}\mspace{14mu}(\%)} = {100 \times \frac{{SI}_{Post} - {SI}_{Pre}}{{SI}_{PRE}}}} & {{Eq}.\mspace{14mu} 1}\end{matrix}$

An observation of signal enhancement in MRI of an amyloid-positiveanimal (as determined by immunofluorescence) was counted as a truepositive result. Conversely, the absence of signal enhancement betweenpre-contrast and delayed post-contrast images for an amyloid-negativeanimal was considered a true negative. Sensitivity was determined by theratio of MRI-identified true positives to the total number of truepositives identified by the gold standard of post-mortem amyloid plaquestaining through immunofluorescence analysis. Specificity was determinedas the ratio of MRI-identified true negatives to the total number oftrue negatives. Overall accuracy was calculated as the total number ofanimals correctly identified by MRI compared with post-mortemimmunofluorescence-determined amyloid true positives.

WT mice (amyloid-negative) did not demonstrate brain signal enhancementin delayed post-contrast images acquired using T1w-SE or FSE-IR at anydose level of ADx-001. However, Tg mice (amyloid-positive) demonstratedmoderate to high MR signal enhancement in the cortical and hippocampalregions in T1w-SE delayed post-contrast images at ADx-001 dose of 0.20and 0.15 mmol Gd/kg. Thus, as shown in FIG. 8: a) a WT animaladministered 0.2 mmol Gd/kg of ADx-001 shows no signal enhancement fourdays after injection; b) a Tg animal shows high enhancement in cortical(upper arrow) and hippocampal regions (lower arrow) four days afteradministration of 0.2 mmol Gd/kg of ADx-001; c) a Tg animal showsmoderate enhancement in cortical (upper arrow) and hippocampal (lowerarrow) regions four days after administration of 0.15 mmol Gd/kg ofADx-001; and d) a Tg animal shows low enhancement in cortical region(arrow) four days after administration of 0.10 mmol Gd/kg of ADx-001.

Similarly, Tg mice demonstrated moderate to high signal enhancement indelayed post-contrast FSE-IR images at an ADx-001 dose of 0.20 and 0.15mmol Gd/kg, and relatively mild signal enhancement at 0.10 mmol Gd/kg.As shown in FIG. 9, FSE-IR axial images demonstrate MR signalenhancement in ADx-001 delayed post-contrast scans of Tg APPswe/PSEN1dE9mice but not in age-matched, WT control mice. Specifically: (a) a WTanimal administered 0.20 mmol Gd/kg ADx-001 demonstrates no signalenhancement in delayed post-contrast images; (b) a Tg animaladministered 0.20 mmol Gd/kg ADx-001 shows high signal enhancement inthe cortical (upper arrow) and hippocampal (lower arrow) regions indelayed post-contrast images; (c) a Tg animal administered 0.15 mmolGd/kg ADx-001 shows moderate signal enhancement in cortical region(upper arrow) and low enhancement in hippocampal region (lower arrow) indelayed post-contrast images; and (d) a Tg animal administered 0.10 mmolGd/kg ADx-001 shows low signal enhancement in cortical region (arrow) indelayed post-contrast images. All delayed post-contrast images wereacquired four days after administration of ADx-001.

Quantitative analysis of cortical ROIs confirmed qualitativeobservations of MR signal enhancement in post-contrast delayed imagesand found a statistically significant difference in post-contrast signalchange between Tg and WT animals at all dose levels. As shown in FIG.10, Tg mice demonstrate MR signal enhancement in cortical brain regionsrelative to WT counterparts at all dose levels of ADx-001. Specifically,box plots show signal changes (expressed as percentage) betweenpre-contrast and delayed post-contrast T1w-SE images for: a) 0.20 mmolGd/kg; b) 0.15 mmol Gd/kg; and c) 0.10 mmol Gd/kg dose levels ofADx-001. Similar signal changes are shown between pre-contrast anddelayed post-contrast FSE-IR images for: d) 0.20 mmol Gd/kg; e) 0.15mmol Gd/kg; and f) 0.10 mmol Gd/kg dose levels. A Wilcoxon rank-sumstatistical test was applied to compare group differences. Values ofp≤0.05 were considered statistically significant. In FIG. 10, p<0.05 (*)and p<0.005 (**).

A signal variance threshold was estimated from pre-contrast (baseline)scans of all tested mice after establishing that the pre-contrast signalfor WT and Tg mice was indistinguishable (see FIG. 11). Estimatedbaseline signal thresholds were: 5.1% (FSE-IR) and 5.6% (T1w-SE).Amyloid-positive mice were identified if they demonstrated signalenhancement above these cutoffs.

Using these thresholds, ADx-001 demonstrated excellent specificity(100%) at all dose levels using both T1w-SE and FSE-IR sequences. Asshown in Table 2, below, in T1w-SE imaging, ADx-001 demonstrated highsensitivity (>80%) at 0.20 and 0.10 mmol Gd/kg dose levels, whereas inFSE-IR imaging, ADx-001 demonstrated high sensitivity (>80%) at the 0.20and 0.15 mmol Gd/kg dose levels. In both T1w-SE and FSE-IR, ADx-001demonstrated the highest accuracy (>90%) at the highest dose level (0.20mmol Gd/kg).

TABLE 2 T1w-SE FSE-IR ADx-001 Dose Accu- Sensi- Speci- Accu- Sensi-Speci- (mmol Gd/kg) racy tivity ficity racy tivity ficity 0.20  100% 100% 100% 91.7% 83.3% 100% 0.15 83.3% 66.7% 100% 91.7% 83.3% 100% 0.1091.7% 83.3% 100%   75%   50% 100%

Longitudinal imaging studies in WT and Tg mice demonstrated that signalenhancement was optimal four days post-contrast administration, and thatsignal had returned to near baseline levels by 21 days post-contrastadministration (see FIG. 12).

Immunofluorescence microscopy analysis confirmed preferentialconcentration and co-localization of ADx-001 with amyloid plaquedeposits in cortex and hippocampus regions in Tg mice. In comparison, WTanimals did not demonstrate amyloid plaque deposits or show the presenceof bound ADx-001 nanoparticles. FIG. 13 shows representativefluorescence microscopy images of ADx-001 binding to amyloid plaques inmouse cortex a) and hippocampus b) regions in a Tg animals.Representative images are also shown for WT cortex c) and hippocampus d)regions. WT mice did not show evidence of amyloid plaque deposits (4G8antibody staining) or presence of bound ADx-001 (observing for amyloidligand fluorescence signal). Images were acquired at 60× magnification.

Example 5: Pharmacokinetic Studies

The pharmacokinetics (“PK”) of ADx-001 were evaluated in cynomolgusmonkeys and beagle dogs. Non-naïve male cynomolgus monkeys (n=3, 2-5 yrage, 2.3-3.1 kg body weight) were intravenously administered ADx-001using a calibrated infusion pump over ˜60 min at 0.30 mmol Gd/kg. Bloodsamples were collected from all animals at pre-dose, immediatelypost-end of infusion, and 4, 8, 24, 48, 96, 168, 336, and 672 hourspost-start of injection (“SOT”). For PK analysis in beagle dogs, animals(n=5, 5-7 months age, 6.2-7.9 kg body weight) were intravenously infusedADx-001 over ˜60 min at 0.30 mmol Gd/kg. Blood samples were processed toplasma and stored frozen until ready for analysis.

Gd concentration in plasma samples was determined using ICP-MS. Plasmasamples (100 μL) were digested in 90% concentrated HNO₃ (750 μL) at 90°C. for 15 min. The digested samples were diluted in deionized (“DI”)water, centrifuged at 3000 rpm for 15 min, and the supernatant wasfurther diluted for ICP-MS analysis such that the Gd concentrations fellwithin the range of ICP-MS calibration standards (1-500 ppb).

ADx-001 was well tolerated in dogs and monkeys with no adverse effects.FIG. 14 demonstrates a long blood half-life for ADx-001. Plasma Gdconcentrations were determined using ICP-MS at various time points afteradministration of ADx-001 to the dogs (▴) and monkeys (●). Assumingfirst-order kinetics, the elimination rate was 0.017 hour⁻¹, resultingin a blood half-life of approximately 41 hours in monkeys. Plasma levelsof Gd declined by ˜80% at 96 hours post-SOI and by greater than 99% at336 hours post-SOI in monkeys. While there is a lack of literature onblood half-life of comparable liposome-based MRI contrast agents inmonkeys, studies in mice have shown a blood half-life in the 14-24 hrrange. In dogs, the elimination rate was 0.0297 hr⁻¹, resulting in ablood half-life of approximately 23 hours. Plasma levels of Gd declinedby ˜85% at 96 hours post-SOI and ˜99% at 168 hr post-SOI in dogs.

Example 6: Tissue Biodistribution

The biodistribution of ADx-001 was studied in a rat model. Wistar Hanrats (10 weeks age, 257-296 g body weight; n=13 per treatment group)were administered ADx-001 at 0.15 mmol Gd/kg (n=13) or 0.30 mmol Gd/kgas a single intravenous bolus injection. Animals were euthanized at Day4 (n=7/dose level) and Day 28 (n=6/dose level) post-administration ofADx-001. Tissues were harvested to determine Gd levels in target organs(liver, spleen, kidney, skin, bone, and brain). Tissue samples werefrozen immediately in liquid nitrogen and stored at −20° C. until readyfor analysis.

Gd concentration in tissue samples was quantified using ICP-MS. Wettissue (˜100 mg) was digested in 90% concentrated HNO₃ (˜750 μL) at 90°C. for 10-15 min. The digested sample was diluted in DI water, vortexedvigorously, and centrifuged at 3500 rpm for 15 min. The supernatant wasseparated and further diluted as needed to ensure Gd concentrations fellwithin the range of calibration standards (1-500 ppb). Quality controlsamples (50 and 100 ppb) were included at the start, middle, and end ofanalysis runs.

ADx-001 was well tolerated in rats at doses up to 0.30 mmol Gd/kg, withno observable adverse effects on clinical toxicity, clinical pathology,or histopathology endpoints (data not shown). Tissue Gd levels showed adose-related increase in all organs. Thus, FIG. 15 shows ICP-MS analysesillustrating the Gd levels in a) spleen; b) liver; c) kidney; d) bone;e) skin; and f) brain at day 4 and day 28 after intravenousadministration of ADx-001 at 0.15 mmol Gd/kg dose level (▴) and 0.3 mmolGd/kg dose level (●). Tissue Gd content is expressed as mg Gd per gramof wet tissue. The highest Gd tissue levels were observed in liver andspleen, consistent with known organs for clearance of PEGylatedliposomal agents. The lowest Gd levels were observed in the brain.Tissue levels of Gd at day 28 were reduced by more than 90% compared toGd tissue levels at day 4 in all organs.

Animal studies were performed under a protocol approved by theInstitutional Animal Care and Use Committee. The studies were incompliance with NC3RS-ARRIVE guidelines.

ADx-001-enhanced MRI demonstrated significantly higher (p<0.05) brainsignal enhancement in Tg mice (amyloid-positive) relative to WT(amyloid-negative) mice at all dose levels. ADx-001-enhanced T1w-SEimaging demonstrated high sensitivity (>80%) at 0.10 and 0.20 mmolGd/kg, whereas ADx-001-enhanced FSE-IR imaging demonstrated highsensitivity (>80%) at 0.15 and 0.20 mmol Gd/kg. Excellent specificity(100%) was observed at all dose levels of ADx-001. Pharmacokineticstudies demonstrated long blood half-life (23 hours in dogs and 41 hoursin monkeys). Biodistribution studies demonstrated systemic clearance ofADx-001 primarily via the mononuclear phagocytic system (also known asthe reticuloendothelial system). Tissue Gd levels in all organs at day28 were reduced by greater than 90% compared to day 4, suggestingon-going clearance.

In short, the amyloid-targeted liposomal macrocyclic gadolinium contrastagent, ADx-001, demonstrated high sensitivity and excellent specificityfor in vivo imaging of β-amyloid plaques in mouse brain. No signs oftoxicity were detected, and the pharmacokinetics followed expectedpatterns for PEGylated nanoparticles.

Unless otherwise specified, “a,” “an,” “the,” “one or more of,” and “atleast one” are used interchangeably. The singular forms “a”, “an,” and“the” are inclusive of their plural forms. The recitations of numericalranges by endpoints include all numbers subsumed within that range(e.g., 1 to 5 includes 1, 1.5, 2, 2.75, 3, 3.80, 4, 5, etc.). The terms“comprising” and “including” are intended to be equivalent andopen-ended. The phrase “consisting essentially of” means that thecomposition or method may include additional ingredients and/or steps,but only if the additional ingredients and/or steps do not materiallyalter the basic and novel characteristics of the claimed composition ormethod. The phrase “selected from the group consisting of” is meant toinclude mixtures of the listed group.

1. A liposomal composition, comprising: a first phospholipid; asterically bulky excipient that is capable of stabilizing the liposomalcomposition; a second phospholipid that is derivatized with a firstpolymer; a macrocyclic gadolinium-based imaging agent; and a thirdphospholipid that is derivatized with a second polymer, the secondpolymer being conjugated to a targeting ligand, the targeting ligandbeing represented by:

wherein, Pyrimidine “P” may be substituted with zero, one, or more of—OH, O-alkyl, and —NH₂; R² is a linking group comprising C₁-C₆ alkyl orC₁-C₆ alkoxyalkyl; and R³ is hydrogen, C₁-C₆ alkyl, or C₁-C₆alkoxyalkyl, and R³ other than hydrogen is substituted with zero, one,or more —OH.
 2. The liposomal composition of claim 1, wherein the firstphospholipid comprises hydrogenated soy L-α-phosphatidylcholine(“HSPC”).
 3. The liposomal composition of claim 1, wherein thesterically bulky excipient that is capable of stabilizing the liposomalcomposition comprises cholesterol (“Chol”).
 4. The liposomal compositionof claim 1, wherein the second phospholipid that is derivatized with afirst polymer comprises1,2-distearoyl-sn-glycero-3-phosphoethanolamine-N-(methoxy (polyethyleneglycol)-2000) (“DSPE-mPEG2000”).
 5. The liposomal composition of claim1, wherein the macrocyclic gadolinium-based imaging agent comprises:


6. The liposomal composition of claim 1, wherein the macrocyclicgadolinium-based imaging agent is selected from the group consisting of:


7. The liposomal composition of claim 5, wherein the macrocyclicgadolinium-based imaging agent is conjugated to a fourth phospholipid tocomprise:

or a salt thereof, and wherein the variable x is one of: 12, 13, 14, 15,16, 17, or
 18. 8. The liposomal composition of claim 7, wherein thevariable x is 16 (the conjugate: “Gd(III)-DOTA-DSPE”).
 9. The liposomalcomposition of claim 1, wherein the targeting ligand comprises:


10. The liposomal composition of claim 1, wherein the third phospholipidthat is derivatized with a second polymer comprises:

or a salt thereof, wherein the variable n is any integer from about 70to about 90, and wherein the variable m is one of: 12, 13, 14, 15, 16,17, or
 18. 11. The liposomal composition of claim 1, wherein theconjugate of the third phospholipid, the second polymer, and thetargeting ligand comprises:


12. A liposomal composition, comprising: a macrocyclic gadolinium-basedimaging agent comprising:

and a first phospholipid that is derivatized with a polymer, the polymerbeing conjugated to a targeting ligand, the targeting ligand beingrepresented by:

wherein, Pyrimidine “P” may be substituted with zero, one, or more of—OH, O-alkyl, and —NH₂; R² is a linking group comprising C₁-C₆ alkyl orC₁-C₆ alkoxyalkyl; and R³ is hydrogen, C₁-C₆ alkyl, or C₁-C₆alkoxyalkyl, and R³ other than hydrogen is substituted with zero, one,or more —OH.
 13. The liposomal composition of claim 12, wherein: themacrocyclic gadolinium-based imaging agent is conjugated to a secondphospholipid to comprise:

or a salt thereof, and wherein the variable x is one of: 12, 13, 14, 15,16, 17, or 18; and the conjugate of the first phospholipid, the polymer,and the targeting ligand comprises:

or a salt thereof, wherein the variable n is any integer from about 70to about 90, and wherein the variable m is one of: 12, 13, 14, 15, 16,17, or
 18. 14. A liposomal composition, comprising: liposomes, theliposomes comprising; HSPC; Chol; DSPE-mPEG2000; Gd(III)-DOTA-DSPE; andET3-73.
 15. The liposomal composition of claim 14, wherein a molar ratio(%) of components in the liposomal composition isHSPC:Chol:DSPE-mPEG2000:Gd(III)-DOTA-DSPE:ET3-73=about 31.5:about40:about 2.5:about 25:about
 1. 16. The liposomal composition of claim14, wherein a molar ratio (%) of components in the liposomal compositionis HSPC:Chol:DSPE-mPEG2000:Gd(III)-DOTA-DSPE:ET3-73=about 32.5:about40:about 2:about 25:about 0.5.
 17. The liposomal composition of claim14, wherein the average diameter (D₅₀) of the liposomes in the liposomalcomposition is between about 100 nm to about 140 nm.
 18. The liposomalcomposition of claim 14, wherein the liposomal composition has a pH ofbetween 6.4 and 8.4.
 19. The liposomal composition of claim 14,comprising a free gadolinium content of less than 2.5 μg/mL.
 20. Theliposomal composition of claim 14, wherein the liposomes have anosmolality of between 200-400 mOsmol/kg.